US6641617B1 - Radiation and melt treated ultra high molecular weight polyethylene prosthetic device and method - Google Patents

Radiation and melt treated ultra high molecular weight polyethylene prosthetic device and method Download PDF

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Publication number
US6641617B1
US6641617B1 US09/454,123 US45412399A US6641617B1 US 6641617 B1 US6641617 B1 US 6641617B1 US 45412399 A US45412399 A US 45412399A US 6641617 B1 US6641617 B1 US 6641617B1
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United States
Prior art keywords
prosthesis
uhmwpe
molecular weight
high molecular
ultra high
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Lifetime
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US09/454,123
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English (en)
Inventor
Edward W. Merrill
William H. Harris
Murali Jasty
Orhun Muratoglu
Charles R. Bragdon
Daniel O. O'Connor
Premnath Venugopalan
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
General Hospital Corp
Zimmer Technology Inc
Massachusetts Institute of Technology
Zimmer Austin Inc
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General Hospital Corp
Massachusetts Institute of Technology
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Priority claimed from US08/600,744 external-priority patent/US5879400A/en
Application filed by General Hospital Corp, Massachusetts Institute of Technology filed Critical General Hospital Corp
Priority to US09/454,123 priority Critical patent/US6641617B1/en
Assigned to UBS AG, STAMFORD BRANCH AS SECURITY AGENT FOR THE SECURED PARTIES reassignment UBS AG, STAMFORD BRANCH AS SECURITY AGENT FOR THE SECURED PARTIES SECURITY INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: CENERPULSE SPINE-TECH INC., CORPORATION, DELAWARE, CENTERPULSE DENTAL INC., CORPORATION, DELAWARE, CENTERPULSE LTD., LIMITED LIABILITY COMPANY, SWITZERLAND, CENTERPULSE ORTHOPEDICS INC., CENTERPULSE ORTHOPEDICTS LTD., LIMITED LIABILITY COMPANY, SWITZERLAND, CENTERPULSE USA HOLDING CO., CORPORATION, DELAWARE, CENTERPULSE USA INC., CORPORATION, DELAWARE, SULZER CARBOMEDICS INC., CORPORATION, DELAWARE
Assigned to CENTERPULSE ORTHOPEDICS INC. reassignment CENTERPULSE ORTHOPEDICS INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: SULZER ORTHOPEDICS INC.
Assigned to ZIMMER TECHNOLOGY, INC. reassignment ZIMMER TECHNOLOGY, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: ZIMMER, INC.
Application granted granted Critical
Publication of US6641617B1 publication Critical patent/US6641617B1/en
Assigned to CENTERPULSE USA INC. reassignment CENTERPULSE USA INC. PATENT RELEASE AGREEMENT Assignors: UBS AG, STAMFORD BRANCH
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    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
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    • C08F110/00—Homopolymers of unsaturated aliphatic hydrocarbons having only one carbon-to-carbon double bond
    • C08F110/02—Ethene
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00—Stock material or miscellaneous articles
    • Y10T428/31504—Composite [nonstructural laminate]
    • Y10T428/31678—Of metal
    • Y10T428/31692—Next to addition polymer from unsaturated monomers
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
    • Y10T428/00—Stock material or miscellaneous articles
    • Y10T428/31504—Composite [nonstructural laminate]
    • Y10T428/31855—Of addition polymer from unsaturated monomers

Definitions

  • the present invention relates to the orthopedic field and the provision of prostheses, such as hip and knee implants, as well as methods of manufacture of such devices and material used therein.
  • macrophage-induced resorption of the periprosthetic bone is initiated.
  • the macrophage often being unable to digest these polyethylene particles, synthesize and release large numbers of cytokines and growth factors which can ultimately result in bone resorption by osteoclasts and monocytes. This osteolysis can contribute to mechanical loosening of the prosthesis components, thereby sometimes requiring revision surgery with its concomitant problems.
  • UHMWPE radiation treated ultra high molecular weight polyethylene
  • Still another object of the invention is to provide improved UHMWPE which has a high density of cross-links and no detectable free radicals.
  • a still further object of the invention is to provide improved UHMWPE which has improved wear resistance.
  • a medical prosthesis for use within the body which is formed of radiation treated ultra high molecular weight polyethylene (UHMWPE) having substantially no detectable free radicals, is provided.
  • the radiation can be, e.g., gamma or electron radiation.
  • the UHMWPE has a cross-linked structure, is substantially not oxidized, is substantially oxidation resistant, and has substantially no chain scission.
  • part of the prosthesis is in the form of a cup or tray shaped article having a load bearing surface made of this UHMWPE. This load bearing surface can be in contact with a second part of the prosthesis having a mating load bearing surface of a metallic or ceramic material.
  • Another aspect of the invention is radiation treated UHMWPE having substantially no detectable free radicals.
  • this UHMWPE has a cross-linked structure.
  • this UHMWPE is substantially oxidation resistant.
  • fabricated articles e.g., with a load bearing surface, and wear resistant coatings, made from such UHMWPE.
  • One embodiment is where the fabricated article is in the form of a bar stock which is capable of being shaped into articles by conventional methods, e.g., machining.
  • Yet another aspect of the invention includes a method for making a cross-linked UHMWPE having substantially no detectable free radicals.
  • Conventional UHMWPE having polymeric chains is provided. This UHMWPE is irradiated so as to cross-link said polymeric chains.
  • the UHMWPE is heated above the melting temperature of the UHMWPE so that there are substantially no detectable free radicals in the UHMWPE.
  • the UHMWPE is then cooled to room temperature. In certain embodiments, the cooled UHMWPE is machined and/or sterilized.
  • CIR-SM cold irradiation and subsequent melting.
  • the UHMWPE that is provided is at room temperature or below room temperature.
  • WIR-SM i.e., warm irradiation and subsequent melting.
  • the UHMWPE that is provided is pre-heated to a temperature below the melting temperature of the UHMWPE.
  • WIR-AM warm irradiation and adiabatic melting.
  • the UHMWPE that is provided is pre-heated to a temperature below the melting temperature of the UHMWPE, preferably between about 100° C. to below the melting temperature of the UHMWPE.
  • the UHMWPE is in an insulating material so as to reduce heat loss from the UHMWPE during processing.
  • the pre-heated UHMWPE is then irradiated to a high enough total dose and at a fast enough dose rate so as to generate enough heat in the polymer to melt substantially all the crystals in the material and thus ensure elimination of substantially all detectable free radicals generated by, e.g., the irradiating step. It is preferred that the irradiating step use electron irradiation so as to generate such adiabatic heating.
  • Yet another aspect of this invention is the product made in accordance with the above described method.
  • the invention also features a method of making a medical prosthesis from UHMWPE having substantially no detectable free radicals, the prosthesis resulting in reduced production of particles from the prosthesis during wear of the prosthesis.
  • Radiation treated UHMWPE having no detectable free radicals is provided.
  • a medical prosthesis is formed from this UHMWPE so as to reduce production of particles from the prosthesis during wear of the prosthesis, the UHMWPE forming a load bearing surface of the prosthesis. Formation of the prosthesis can be accomplished by standard procedures known to those skilled in the art, e.g., machining.
  • Also provided in this invention is a method of treating a body in need of a medical prosthesis.
  • a shaped prosthesis formed of radiation treated UHMWPE having substantially no detectable free radicals is provided.
  • the prosthesis is applied to the body in need of the prosthesis.
  • the prosthesis reduces production of particles from the prosthesis during wear of the prosthesis.
  • the UHMWPE forms a load bearing surface of the prosthesis.
  • FIG. 1 is a cross-sectional view through the center of a medical hip joint prosthesis in accordance with a preferred embodiment of this invention
  • FIG. 2 is a side view of an acetabular cup liner as shown in FIG. 1;
  • FIG. 3 is a cross-sectional view through line 3 — 3 of FIG. 2;
  • FIG. 4 is a graph showing the crystallinity and melting point of melt-irradiated UHMWPE at different irradiation doses
  • FIG. 5 is an environmental scanning electron micrograph of an etched surface of conventional UHMWPE showing its crystalline structure
  • FIG. 6 is an environmental scanning electron micrograph of an etched surface of melt-irradiated UHMWPE showing its crystalline structure at approximately the same magnification as in FIG. 5;
  • FIG. 7 is a graph showing the crystallinity and melting point at different depths of a melt-irradiated UHMWPE cup.
  • This invention provides a medical prosthesis for use within the body which is formed of radiation treated ultra high molecular weight polyethylene (UHMWPE) which has substantially no detectable free radicals.
  • UHMWPE radiation treated ultra high molecular weight polyethylene
  • a medical prosthesis in the form of a hip joint prosthesis is generally illustrated at 10 in FIG. 1 .
  • the prosthesis shown has a conventional ball head 14 connected by a neck portion to a stem 15 which is mounted by conventional cement 17 to the femur 16 .
  • the ball head can be of conventional design and formed of stainless steel or other alloys as known in the art.
  • the radius of the ball head closely conforms to the inner cup radius of an acetabular cup liner 12 which can be mounted in cement 13 directly to the pelvis 11 .
  • a metallic acetabular cup can be cemented to the pelvis and the cup liner 12 can form a coating or liner connected to the cup by cement or other means as known in the art.
  • the specific form of the prosthesis can vary greatly as known in the art. Many hip joint constructions are known and other prostheses such as knee joints, shoulder joints, ankle joints, elbow joints and finger joints are known. All such prior art prostheses can be benefited by making at least one load bearing surface of such prosthesis of a high molecular weight polyethylene material in accordance with this invention. Such load bearing surfaces can be in the form of layers, linings or actual whole devices as shown in FIG. 1 . In all cases, it is preferred that the load bearing surface act in conjunction with a metallic or ceramic mating member of the prosthesis so that a sliding surface is formed therebetween. Such sliding surfaces are subject to breakdown of the polyethylene as known in the prior art. Such breakdown can be greatly diminished by use of the materials of the present invention.
  • FIG. 2 shows the cup liner in the form of a half hollow ball-shaped device better seen in the cross-section of FIG. 3 .
  • the outer surface 20 of the cup liner need not be circular or hemispherical but can be square or of any configuration to be adhered directly to the pelvis or to the pelvis through a metallic cup as known in the art.
  • the radius of the cup liner shown at 21 in FIG. 3 of the preferred embodiment ranges from about 20 mm to about 35 mm.
  • the thickness of the cup liner from its generally hemispherical hollow portion to the outer surface 20 is preferably about 8 mm.
  • the outer radius is preferably in the order of about 20 mm to about 35 mm.
  • the ball joint can be made of the UHMWPE of this invention and the cup formed of metal, although it is preferred to make the cup or cup liner of UHMWPE to mate with the metallic ball.
  • the particular method of attachment of the components of the prosthesis to the bones of the body can vary greatly as known in the art.
  • the medical prosthesis includes, e.g., orthopedic joint and bone replacement parts, e.g., hip, knee, shoulder, elbow, ankle or finger replacements.
  • the prosthesis can be in the form, e.g., of a cup or tray shaped article which has a load bearing surface.
  • Other forms known to those skilled in the art are also included in the invention.
  • Medical prostheses are also meant to include any wearing surface of a prosthesis, e.g., a coating on a surface of a prosthesis in which the prosthesis is made from a material other than the UHMWPE of this invention.
  • the prostheses of this invention are useful for contact with metal containing parts formed of, e.g., stainless steel, titanium alloy or nickel cobalt alloy, or with ceramic containing parts.
  • a hip joint is constructed in which a cup shaped article having an inner radius of 25 mm, is contacted with a metal ball having an outer radius of 25 mm, so as to closely mate with the cup shaped article.
  • the load bearing surface of the cup shaped article of this example is made from the UHMWPE of this invention, preferably having a thickness of at least about 1 mm, more preferably having a thickness of at least about 2 mm, more preferably having a thickness of at least about 1 ⁇ 4 inch, and more preferably yet having a thickness of at least about 1 ⁇ 3 inch.
  • the prostheses can have any standard known form, shape, or configuration, or be a custom design, but have at least one load bearing surface of UHMWPE of this invention.
  • the prostheses of this invention are non-toxic to humans. They are not subject to deterioration by normal body constituents, e.g., blood or interstitial fluids. They are capable of being sterilized by standard means, including, e.g., heat or ethylene oxide.
  • UHMWPE linear non-branched chains of ethylene that have molecular weights in excess of about 500,000, preferably above about 1,000,000, and more preferably above about 2,000,000. Often the molecular weights can reach about 8,000,000.
  • initial average molecular weight is meant the average molecular weight of the UHMWPE starting material, prior to any irradiation.
  • UHMWPE which has been treated with radiation, e.g., gamma radiation or electron radiation, so as to induce cross-links between the polymeric chains of the UHMWPE.
  • radiation treated UHMWPE UHMWPE which has been treated with radiation, e.g., gamma radiation or electron radiation, so as to induce cross-links between the polymeric chains of the UHMWPE.
  • substantially no detectable free radicals substantially no free radicals as measured by electron paramagnetic resonance, as described in Jahan et al., J. Biomedical Materials Research 25:1005 (1991).
  • Free radicals include, e.g., unsaturated trans-vinylene free radicals.
  • UHMWPE that has been irradiated below its melting point with ionizing radiation contains cross-links as well as long-lived trapped free radicals. These free radicals react with oxygen over the long-term and result in the embrittlement of the UHMWPE through oxidative degradation.
  • An advantage of the UHMWPE and medical prostheses of this invention is that radiation treated UHMWPE is used which has no detectable free radicals.
  • the free radicals can be eliminated by any method which gives this result, e.g., by heating the UHMWPE above its melting point such that substantially no residual crystalline structure remains. By eliminating the crystalline structure, the free radicals are able to recombine and thus are eliminated.
  • the UHMWPE which is used in this invention has a cross-linked structure.
  • An advantage of having a cross-linked structure is that it will reduce production of particles from the prosthesis during wear of the prosthesis.
  • the UHMWPE be substantially not oxidized.
  • substantially not oxidized is meant that the ratio of the area under the carbonyl peak at 1740 cm ⁇ 1 in the FTIR spectra to the area under the peak at 1460 cm ⁇ 1 in the FTIR spectra of the cross-linked sample be of the same order of magnitude as the ratio for the sample before cross-linking.
  • the UHMWPE be substantially oxidation resistant.
  • substantially oxidation resistant is meant that it remains substantially not oxidized for at least about 10 years.
  • it remains substantially not oxidized for at least about 20 years, more preferably for at least about 30 years, more preferably yet for at least about 40 years, and most preferably for the entire lifetime of the patient.
  • the UHMWPE have substantially no chain scission.
  • substantially no chain scission is meant that the fraction of the polymer sample dissolving in normal xylene at 130° C. or decalin at 150° C. and remaining in solution after cooling to room temperature be less than or equal to the fraction of the conventional UHMWPE dissolving in normal xylene at 130° C. or decalin at 150° C. and remaining in solution after cooling to room temperature within the margins of experimental error.
  • the polymeric structure has extensive cross-linking such that a substantial portion of the polymeric structure does not dissolve in xylene or decalin. By substantial portion is meant at least 50% of the polymer sample's dry weight. By not dissolve in xylene or decalin is meant does not dissolve in xylene at 130° C. or decalin at 150° C. over a period of 24 hours.
  • the polymeric structure of the UHMWPE used in the prostheses of this invention results in the reduction of production of UHMWPE particles from the prosthesis during wear of the prosthesis. As a result of the limited number of particles being shed into the body, the prosthesis exhibits longer implant life.
  • the prosthesis can remain implanted in the body for at least 10 years, more preferably for at least 20 years and most preferably for the entire lifetime of the patient.
  • the invention also includes other fabricated articles made from radiation treated UHMWPE having substantially no detectable free radicals.
  • the UHMWPE which is used for making the fabricated articles has a cross-linked structure.
  • the UHMWPE is substantially oxidation resistant.
  • Such articles include shaped articles and unshaped articles, including, e.g., machined or molded objects, e.g., cups, gears, nuts, sled runners, bolts, fasteners, cables and the like, and bar stock, films, cylindrical bars, sheeting, panels, and fibers. Shaped articles can be made, e.g., by machining.
  • the fabricated articles are particularly suitable for load bearing applications, e.g., as a load bearing surface, and as metal replacement articles. Thin films or sheets of the UHMWPE of this invention can also be attached, e.g., with glue, onto supporting surfaces, and thus used as a wear resistant load bearing surface.
  • the invention also includes radiation treated UHMWPE which has substantially no detectable free radicals.
  • the UHMWPE has a cross-linked structure.
  • the UHMWPE is substantially oxidation resistant.
  • certain impurities may be present in the UHMWPE of this invention, including, e.g., calcium stearate, mold release agents, extenders, anti-oxidants and/or other conventional additives to polyethylene polymers.
  • the invention also provides a method for making cross-linked UHMWPE having substantially no detectable free radicals.
  • this UHMWPE is for use as a load bearing article.
  • Conventional UHMWPE having polymeric chains is provided.
  • the conventional UHMWPE can be in the form of, e.g., a bar stock, a shaped bar stock, a coating, or a fabricated article, e.g., a cup or tray shaped article for use in a medical prosthesis.
  • conventional UHMWPE is meant commercially available high density (linear) polyethylene of molecular weights greater than about 500,000.
  • the UHMWPE starting material has an average molecular weight of greater than about 2 million.
  • initial average molecular weight is meant the average molecular weight of the UHMWPE starting material, prior to any irradiation.
  • the UHMWPE is irradiated so as to cross-link the polymeric chains.
  • the irradiation can be done in an inert or non-inert environment.
  • the irradiation is done in a non-inert environment, e.g., air.
  • the irradiated UHMWPE is heated above the melting temperature of the UHMWPE so that there are substantially no detectable free radicals in the UHMWPE.
  • the heated UHMWPE is then cooled to room temperature.
  • the cooling step is at a rate greater than about 0.1° C./minute.
  • the cooled UHMWPE can be machined. For example, if any oxidation of the UHMWPE occurred during the irradiating step, it can be machined away if desired, by any method known to those skilled in the art. And optionally, the cooled UHMWPE, or the machined UHMWPE, can be sterilized by any method known to those skilled in the art.
  • the UHMWPE that is provided is at room temperature or below room temperature. Preferably, it is at room temperature.
  • Irradiation of the UHMWPE can be with, e.g., gamma irradiation or electron irradiation.
  • gamma irradiation gives a high penetration depth but takes a longer time, resulting in increased cost of operation and the possibility of more in-depth oxidation.
  • electron irradiation gives more limited penetration depths but takes a shorter time, and hence the cost and the possibility of extensive oxidation is reduced.
  • the irradiation is done so as to cross-link the polymeric chains.
  • the irradiation dose can be varied to control the degree of cross-linking and crystallinity in the final UHMWPE product.
  • the total absorbed dose of the irradiation is about 0.5 to about 1,000 Mrad, more preferably about 1 to about 100 Mrad, more preferably yet about 4 to about 30 Mrad, and most preferably about 20 Mrad.
  • a dose rate is used that does not generate enough heat to melt the UHMWPE. If gamma irradiation is used, the preferred dose rate is about 0.05 to about 0.2 Mrad/minute.
  • the dose rate is about 0.05 to about 3,000 Mrad/minute, more preferably about 0.05 to about 5 Mrad/minute, and most preferably about 0.05 to about 0.2 Mrad/minute.
  • the energy of the electrons can be varied to change the depth of penetration of the electrons.
  • the energy of the electrons is about 0.5 MeV to about 12 MeV, more preferably about 5 MeV to about 12 MeV.
  • Such manipulability is particularly useful when the irradiated object is an article of varying thickness or depth, e.g., an articular cup for a medical prosthesis.
  • the irradiated UHMWPE is heated above the melting temperature of the UHMWPE so that there are no detectable free radicals in the UHMWPE.
  • the heating provides the molecules with sufficient mobility so as to eliminate the constraints derived from the crystals of the UHMWPE, thereby allowing essentially all of the residual free radicals to recombine.
  • the UHMWPE is heated to a temperature of about 137° C. to about 300° C., more preferably about 140° C. to about 300° C., more preferably yet about 140° C. to about 190° C., and most preferably about 150° C.
  • the temperature in the heating step is maintained for about 0.5 minutes to about 24 hours, more preferably about 1 hour to about 3 hours, and most preferably about 2 hours.
  • the heating can be carried out, e.g., in air, in an inert gas, e.g., nitrogen, argon or helium, in a sensitizing atmosphere, e.g., acetylene, or in a vacuum. It is preferred that for the longer heating times, that the heating be carried out in an inert gas or under vacuum.
  • WIR-SM warm irradiation and subsequent melting.
  • the UHMWPE that is provided is pre-heated to a temperature below the melting temperature of the UHMWPE.
  • the pre-heating can be done in an inert or non-inert environment. It is preferred that this pre-heating is done in air.
  • the UHMWPE is pre-heated to a temperature of about 20° C. to about 135° C.; more preferably the temperature is about 50° C.
  • the other parameters are as described above for the CIR-SM embodiment, except that the dose rate for the irradiating step preferably is about 0.05 to about 10 Mrad/minute, and more preferably is about 4 to about 5 Mrad/minute.
  • the UHMWPE that is provided is pre-heated to a temperature below the melting temperature of the UHMWPE.
  • the pre-heating can be done in an inert or non-inert environment. It is preferred that this pre-heating is done in air.
  • the pre-heating can be done, e.g., in an oven. It is preferred that the pre-heating is to a temperature between about 100° C. to below the melting temperature of the UHMWPE.
  • the UHMWPE is pre-heated to a temperature of about 100° C. to about 135° C., more preferably the temperature is about 130° C.
  • the UHMWPE is in an insulating material so as to reduce heat loss from the UHMWPE during processing.
  • the heat is meant to include, e.g., the pre-heat delivered before irradiation and the heat generated during irradiation.
  • insulating material is meant any type of material which has insulating properties, e.g., a fiberglass pouch.
  • the pre-heated UHMWPE is then irradiated to a high enough total dose and at a fast enough dose rate so as to generate enough heat in the polymer to melt substantially all the crystals in the material and thus ensure elimination of substantially all detectable free radicals generated by, e.g., the irradiating step. It is preferred that the irradiating step use electron irradiation so as to generate such adiabatic heating.
  • the minimum total dose is determined by the amount of heat necessary to heat the polymer from its initial temperature (i.e., the pre-heated temperature discussed above) to its melting temperature, and the heat necessary to melt all the crystals, and the heat necessary to heat the polymer to a pre-determined temperature above its melting point. The following equation describes how the amount of total dose is calculated:
  • T i is the initial temperature
  • T f is the final temperature. The final temperature should be above the melting temperature of the UHMWPE.
  • the final temperature of the UHMWPE is about 140° C. to about 200° C., more preferably it is abo or decalin at 150° C. or decalin at 150° C. or decalin at 150° C. or decalin at 150° C. ut 150° C.
  • the polymer starts to form bubbles and cracks.
  • the dose rate of the electron irradiation is about 2 to about 3,000 Mrad/minute, more preferably is about 7 to about 25 Mrad/minute, and most preferably is about 20 Mrad/minute.
  • the total absorbed dose is about 1 to about 100 Mrad. Using the above equation, the absorbed dose for an initial temperature of 130° C. and a final temperature of 150° C. is calculated to be about 22 Mrad.
  • the heating step of the method is the adiabatic heating described above.
  • the method has a second heating step after the adiabatic heating so that the final temperature after the second heating step is above the melting temperature of the UHMWPE.
  • This invention also includes the product made in accordance with the above described method.
  • Also provided in this invention is a method of making a medical prosthesis from UHMWPE having substantially no detectable free radicals, the prosthesis resulting in the reduced production of particles from the prosthesis during wear of the prosthesis.
  • Radiation treated UHMWPE having no detectable free radicals is provided.
  • a medical prosthesis is formed from this UHMWPE so as to reduce production of particles from the prosthesis during wear of the prosthesis, the UHMWPE forming a load bearing surface of the prosthesis. Formation of the prosthesis can be accomplished by standard procedures known to those skilled in the art, e.g., machining.
  • Also provided in this invention is a method of treating a body in need of a medical prosthesis.
  • a shaped prosthesis formed of radiation treated UHMWPE having substantially no detectable free radicals is provided. This prosthesis is applied to the body in need of the prosthesis.
  • the prosthesis reduces production of fine particles from the prosthesis during wear of the prosthesis.
  • the ultra high molecular weight polyethylene forms a load bearing surface of the prosthesis.
  • a medical prosthesis for use within the body which is formed of ultra high molecular weight polyethylene (UHMWPE) which has a polymeric structure with less than about 50% crystallinity, less than about 290 ⁇ lamellar thickness and less than about 940 MPa tensile elastic modulus, so as to reduce production of fine particles from the prosthesis during wear of the prosthesis, is provided.
  • UHMWPE ultra high molecular weight polyethylene
  • the UHMWPE of this embodiment has a polymeric structure with less than about 50% crystallinity, preferably less than about 40% crystallinity, more preferably less than about 35% crystallinity, and most preferably less than about 30% crystallinity.
  • the UHMWPE of this embodiment has a polymeric structure with less than about 290 ⁇ lamellar thickness, preferably less than about 200 ⁇ lamellar thickness, and most preferably less than about 100 ⁇ lamellar thickness.
  • ⁇ e is the end free surface energy of polyethylene (2.22 ⁇ 10 ⁇ 6 cal/cm 2 )
  • ⁇ H is the heat of melting of polyethylene crystals (69.2 cal/g)
  • ⁇ is the density of the crystalline regions (1.005 g/cm 3 )
  • T m ° is the melting point of a perfect polyethylene crystal (418.15K)
  • T m is the experimentally determined melting point of the sample.
  • the UHMWPE of this embodiment has less than about 940 MPa tensile elastic modulus, preferably less than about 600 MPa tensile elastic modulus, more preferably less than about 400 MPa tensile elastic modulus, and most preferably less than about 200 MPa tensile elastic modulus.
  • tensile elastic modulus is meant the ratio of the nominal stress to corresponding strain for strains less than 0.5% as determined using the standard test ASTM 638 M III.
  • the UHMWPE of this embodiment has a polymeric structure with about 40% crystallinity, about 100 ⁇ lamellar thickness and about 200 MPa tensile elastic modulus.
  • the UHMWPE of this embodiment have no trapped free radicals, especially unsaturated trans-vinylene free radicals. It is preferred that the UHMWPE of this embodiment have a hardness less than about 65 on the Shore D scale, more preferably a hardness less than about 55 on the Shore D scale, most preferably a hardness less than about 50 on the. Shore D scale. By hardness is meant the instantaneous indentation hardness measured on the Shore D scale using a durometer described in ASTM D2240. It is preferred that the UHMWPE of this embodiment be substantially not oxidized and/or have substantially no chain scission. In some embodiments, the polymeric structure has extensive cross-linking such that a substantial portion of the polymeric structure does not dissolve in Decalin.
  • the UHMWPE of this embodiment has a high density of entanglement so as to cause the formation of imperfect crystals and reduce crystallinity.
  • the density of entanglement is meant the number of points of entanglement of polymer chains in a unit volume; a higher density of entanglement being indicated by the polymer sample's inability to crystallize to the same extent as conventional UHMWPE, thus leading to a lesser degree of crystallinity.
  • the invention also includes other fabricated articles made from the UHMWPE of this embodiment having a polymeric structure with less than about 50% crystallinity, less than about 290 ⁇ lamellar thickness and less than about 940 MPa tensile elastic modulus.
  • Such articles include shaped articles and unshaped articles, including, e.g., machined or molded objects, e.g., cups, gears, nuts, sled runners, bolts, fasteners, cables and the like, and bar stock, films, cylindrical bars, sheeting, panels, and fibers.
  • Shaped articles can be made, e.g., by machining.
  • the fabricated articles are particularly suitable for load bearing applications, e.g., as a load bearing surface, and as metal replacement articles.
  • Thin films or sheets of UHMWPE, which have been melt-irradiated can also be attached, e.g., with glue, onto supporting surfaces, and thus used as a transparent, wear resistant load bearing surface.
  • the invention also includes an embodiment in which UHMWPE has a unique polymeric structure characterized by less than about 50% crystallinity, less than about 290 ⁇ lamellar thickness and less than about 940 MPa tensile elastic modulus.
  • certain impurities may be present in the UHMWPE of this invention, including, e.g., calcium stearate, mold release agents, extenders, anti-oxidants and/or other conventional additives to polyethylene polymers.
  • the UHMWPE has high transmissivity of light, preferably a transmission greater than about 10% of light at 517 nm through a 1 mm thick sample, more preferably a transmission greater than about 30% of light at 517 nm through a 1 mm thick sample, and most preferably a transmission greater than about 40% of light at 517 nm through a 1 mm thick sample.
  • Such UHMWPE is particularly useful for thin films or sheets which can be attached onto supporting surfaces of various articles, the film or sheet being transparent and wear resistant.
  • a method for making UHMWPE which is highly entangled and crosslinked is provided.
  • This method is called melt irradiation (MIR).
  • MIR melt irradiation
  • this UHMWPE has a polymeric structure with less than about 50% crystallinity, less than about 290 ⁇ lamellar thickness and less than about 940 MPa tensile elastic modulus.
  • Conventional UHMWPE e.g., a powder, a bar stock, a shaped bar stock, a coating, or a fabricated article is provided.
  • conventional UHMWPE is meant commercially available high density (linear) polyethylene of molecular weights greater than about 500,000.
  • the UHMWPE starting material has an average molecular weight of greater than about 2 million.
  • initial average molecular weight is meant the average molecular weight of the UHMWPE starting material, prior to any irradiation.
  • This UHMWPE is surrounded with an inert material that is substantially free of oxygen, e.g., nitrogen, argon or helium.
  • the UHMWPE is heated above its melting temperature for a time sufficient to allow the UHMWPE chains to take up an entangled state.
  • the temperature is about 145° C. to about 230° C., and more preferably, is about 175° to about 200° C.
  • the period of time of heating should be sufficient to permit the UHMWPE polymer chains to take up a random coil conformation.
  • the heating is maintained so to keep the polymer at the preferred temperature for about 5 minutes to about 3 hours, and more preferably for about 30 minutes to about 2 hours.
  • the UHMWPE is then irradiated so as to trap the polymer chains in the entangled state, e.g., with gamma irradiation or electron irradiation.
  • gamma irradiation gives a high penetration depth but takes a longer time, resulting in increased cost of operation and the possibility of some oxidation.
  • the irradiation dose can be varied to control the degree of crosslinking and crystallinity in the final UHMWPE product.
  • a dose of greater than about 1 MRad is used, more preferably a dose of greater than about 20 MRad is used.
  • the energy of the electrons can be varied to change the depth of penetration of the electrons, thereby controlling the degree of crosslinking and crystallinity in the final UHMWPE product.
  • the energy is about 0.5 MeV to about 10 MeV, more preferably about 1 MeV to about 5 MeV.
  • the irradiated UHMWPE is then cooled to about 25° C. so as to produce UHMWPE with lower crystallinity than the starting material.
  • Faster cooling rates are preferred.
  • the cooling rate is equal to or greater than about 0.5° C./min, more preferably equal to or greater than about 120° C./min.
  • the cooled UHMWPE can be machined. Examples 1, 3 and 6 describe preferred embodiments of the method. Examples 2, 4 and 5, and FIGS. 4 through 7, illustrate certain properties of the melt-irradiated UHMWPE obtained from these preferred embodiments, as compared to conventional UHMWPE.
  • UHMWPE is standardly generated by Ziegler-Natta catalysis, and as the polymer chains are generated from the surface catalytic site, they crystallize, and interlock as crystal folded chains.
  • Examples of known UHMWPE include Hifax Grade 1900 polyethylene (obtained from Himont USA Corp., Wilmington, Del.) and Hoechst-Celanese GUR-415 polyethylene (obtained from Hoechst-Celanese Corp., Houston, Tex.).
  • This invention also includes the product made in accordance with the above described method.
  • UHMWPE having a polymeric structure with less than about 50% crystallinity, less than about 290 ⁇ lamellar thickness and less than about 940 MPa tensile elastic modulus is provided.
  • a prosthesis is formed from this UHMWPE, the UHMWPE forming a load bearing surface of the prosthesis. Formation of the prosthesis can be accomplished by standard procedures known to those skilled in the art, e.g., machining.
  • This prosthesis is applied to the body in need of the prosthesis.
  • the prosthesis reduces production of fine particles from the prosthesis during wear of the prosthesis.
  • the ultra high molecular weight polyethylene forms a load bearing surface of the prosthesis.
  • the products and processes of this invention also apply to other polymeric materials such as high-density-polyethylene, low-density-polyethylene, linear-low-density-polyethylene and polypropylene.
  • This example illustrates electron irradiation of melted UHMWPE.
  • the atmosphere within the chamber consisted of low oxygen nitrogen gas ( ⁇ 0.5 ppm oxygen gas) (obtained from AIRCO, Murray Hill, N.J.).
  • the pressure in the chamber was approximately 1 atm.
  • the temperature of the sample and the irradiation chamber was controlled using a heater, a variac and a thermocouple readout (manual) or temperature controller (automatic).
  • the chamber was heated with a 270 W heating mantle.
  • the chamber was heated (controlled by the variac) at a rate such that the steady state temperature of the sample was about 175° C.
  • the sample was held at the steady state temperature for 30 minutes before starting the irradiation.
  • Irradiation was done using a van de Graaff generator with electrons of energy 2.5 MeV and a dose rate of 1.67 MRad/min.
  • the sample was given a dose of 20 MRad with the electron beam hitting the sample on the 60 mm ⁇ 12 mm surface.
  • the heater was switched off after irradiation, and the sample was allowed to cool within the chamber under inert atmosphere, nitrogen gas, to 25° C. at approximately 0.5° C./minute.
  • similar specimens were prepared using unheated and unirradiated bar stock of conventional UHMWPE.
  • This example illustrates various properties of the irradiated and unirradiated samples of UHMWPE bar stock (GUR 415) obtained from Example 1.
  • the tested samples were as follows: the test sample was bar stock which was molten and then irradiated while molten; control was bar stock (no heating/melting, no irradiation).
  • a Perkin-Elmer DSC7 was used with an ice-water heat sink and a heating and cooling rate of 10° C./minute with a continuous nitrogen purge.
  • the crystallinity of the samples obtained from Example 1 was calculated from the weight of the sample and the heat of melting of polyethylene crystals (69.2 cal/g). The temperature corresponding to the peak of the endotherm was taken as the melting point.
  • the lamellar thickness was calculated by assuming a lamellar crystalline morphology, and knowing the heat of crystallization (69.2 cal/g), the melting point of a perfect crystal (418.15 K), the density of the crystalline regions (1.005 g/cm 3 ) and the end free surface energy of polyethylene (2.22 ⁇ 10 ⁇ 6 cal/cm 2 ). The results are shown in Table 1 and FIG. 4 .
  • melt-irradiated sample had a more entangled and less crystalline polymeric structure than the unirradiated sample, as evidenced by lower crystallinity, lower lamellar thickness and lower melting point.
  • the samples were cut into cubes of size 2 mm ⁇ 2 mm ⁇ 2 mm and kept submerged in Decalin at 150° C. for a period of 24 hours.
  • An antioxidant 1% N-phenyl-2-naphthylamine
  • the swell ratio and percent extract were calculated by measuring the weight of the sample before the experiment, after swelling for 24 hours and after vacuum drying the swollen sample. The results are shown in Table 2.
  • melt-irradiated UHMWPE sample had a significantly lower tensile elastic modulus than the unirradiated control.
  • the lower strain at break of the melt-irradiated UHMWPE sample is yet further evidence for the crosslinking of chains in that sample.
  • Transparency of the samples was measured as follows: Light transmission was studied for a light of wave length 517 nm passing through a sample of approximately 1 mm in thickness placed between two glass slides. The samples were prepared by polishing the surfaces against 600 grit paper. Silicone oil was spread on the surfaces of the sample and then the sample was placed in between two slides. The silicone oil was used in order to reduce diffuse light scattering due to the surface roughness of the polymer sample. The reference used for this purpose was two similar glass slides separated by a thin film of silicone oil. The transmissivity was measured using a Perkin Elmer Lambda 3B uv-vis spectrophotometer. The absorption coefficient and transmissivity of a sample exactly 1 mm thick were calculated using the Lambert-Beer law. The results are shown in Table 5.
  • ESEM ElectroScan, Model 3
  • 10 kV low voltage to reduce radiation damage to the sample
  • gold coating approximately 20 ⁇ to enhance picture quality
  • the samples were etched using a permanganate etch with a 1:1 sulfuric acid to orthophosphoric acid ratio and a 0.7% (w/v) concentration of potassium permanganate before being viewed under the ESEM.
  • FIG. 4 shows an ESEM (magnification of 10,000 ⁇ ) of an etched surface of conventional UHMWPE (GUR 415; unheated; unirradiated).
  • FIG. 5 shows an ESEM (magnification of 10,500 ⁇ ) of an etched surface of melt-irradiated UHMWPE (GUR 415; melted; 20 MRad).
  • the ESEMs indicated a reduction in size of the crystallites and the occurrence of imperfect crystallization in the melt-irradiated UHMWPE as compared to the conventional UHMWPE.
  • FTIR of the samples was performed using a microsampler on the samples rinsed with hexane to remove surface impurities.
  • the peaks observed around 1740 to 1700 cm ⁇ 1 are bands associated with oxygen containing groups.
  • the ratio of the area under the carbonyl peak at 1740 cm ⁇ 1 to the area under the methylene peak at 1460 cm ⁇ 1 is a measure of the degree of oxidation.
  • the FTIR spectra indicate that the melt-irradiated UHMWPE sample showed more oxidation than the conventional unirradiated UHMWPE control, but a lot less oxidation than an UHMWPE sample irradiated in air at room temperature and given the same irradiation dose as the melt-irradiated sample.
  • EPR was performed at room temperature on the samples which were placed in a nitrogen atmosphere in an air tight quartz tube.
  • the instrument used was the Bruker ESP 300 EPR spectrometer and the tubes used were Taperlok EPR sample tubes obtained from Wilmad Glass Company, Buena, N.J.
  • the unirradiated samples do not have any free radicals in them since irradiation is the process which creates free radicals in the polymer. On irradiation, free radicals are created which can last for several years under the appropriate conditions.
  • the EPR results indicate that the melt-irradiated sample did not show any free radicals when studied using an EPR immediately after irradiation, whereas the sample which was irradiated at room temperature under nitrogen atmosphere showed trans-vinylene free radicals even after 266 days of storage at room temperature.
  • the absence of free radicals in the melt-irradiated UHMWPE sample means that any further oxidative degradation was not possible.
  • the wear resistance of the samples was measured using a bi-axial pin-on-disk wear tester.
  • the unirradiated pin displayed a wear rate of 8 mg/million cycles while the irradiated pin had a wear rate of 0.5 mg/million cycles.
  • the results indicate that the melt-irradiated UHMWPE has far superior wear resistance than the unirradiated control.
  • This example illustrates electron irradiation of a melted UHMWPE conventional articular cup.
  • a conventional articular cup (high conformity unsterilized UHMWPE cup made by Zimmer, Inc., Warsaw, Ind.) of internal diameter 26 mm and made of GUR 415 ram extruded bar stock, was irradiated under controlled atmosphere and temperature conditions in an air-tight chamber with a titanium cup holder at the base and a thin stainless steel foil (0.001 inches thick) at the top.
  • the atmosphere within this chamber consisted of low oxygen nitrogen gas ( ⁇ 0.5 ppm oxygen gas) (obtained from AIRCO, Murray Hill, N.H.).
  • the pressure in the chamber was approximately 1 atm.
  • the chamber was heated using a 270 W heating mantle at the base of the chamber which was controlled using a temperature controller and a variac.
  • the chamber was heated such that the temperature at the top surface of the cup rose at approximately 1.5° to 2° C./min, finally asymptotically reaching a steady state temperature of approximately 175° C. Due to the thickness of the sample cup and the particular design of the equipment used, the steady state temperature of the cup varied between 200° C. at the base to 175° C. at the top. The cup was held at these temperatures for a period of 30 minutes before starting the irradiation.
  • Irradiation was done using a van de Graaff generator with electrons of energy 2.5 MeV and a dose rate of 1.67 MRad/min.
  • the beam entered the chamber through the thin foil at top and hit the concave surface of the cup.
  • the dose received by the cup was such that a maximum dose of 20 MRad was received approximately 5 mm below the surface of the cup being hit by the electrons.
  • the heating was stopped and the cup was allowed to cool to room temperature (approximately 25° C.) while still in the chamber with nitrogen gas.
  • the rate of cooling was approximately 0.5° C./min.
  • the sample was removed from the chamber after the chamber and the sample had reached room temperature.
  • This example illustrates the swell ratio and percent extract at different depths of the melt-irradiated articular cup obtained from Example 3.
  • Samples of size 2 mm ⁇ 2 mm ⁇ 2 mm were cut from the cup at various depths along the axis of the cup. These samples were then kept submerged in Decalin at 150° C. for a period of 24 hours.
  • An antioxidant 1% N-phenyl-2-naphthylamine
  • the swell ratio and percent extract were calculated by measuring the weight of the sample before the experiment, after swelling for 24 hours, and after vacuum drying the swollen sample. The results are shown in Table 6.
  • This example illustrates the crystallinity and melting point at different depths of the melt-irradiated cup obtained from Example 3.
  • the crystallinity is the fraction of the polymer that is crystalline.
  • the melting point is the temperature corresponding to the peak in the DSC endotherm. The results are shown in FIG. 7 .
  • This example illustrates a method for making articular cups with melt-irradiated UHMWPE.
  • Irradiation was done using a van de Graaff generator with electrons of energy 2.5 MeV and a dose rate of 1.67 MRad/min.
  • the beam entered the chamber through the thin foil at top and hit the surface with the hemispherical hole.
  • the dose received by the specimen was such that a maximum dose of 20 MRad was received approximately 5 mm below the surface of the polymer being hit by the electrons.
  • the heating was stopped and the specimen was allowed to cool to room temperature (approximately 25° C.) while still in the chamber with nitrogen gas.
  • the rate of cooling was approximately 0.5° C./min.
  • the sample was removed from the chamber after the chamber and the sample had reached room temperature.
  • This cylindrical specimen was then machined into an articular cup with the dimensions of a high conformity UHMWPE articular cup of internal diameter 26 mm manufactured by Zimmer, Inc., Warsaw, Ind., such that the concave surface of the hemispherical hole was remachined into the articulating surface.
  • This method allows for the possibility of relatively large changes in dimensions during melt irradiation.
  • UHMWPE bar stock made from GUR 415 resin obtained from Westlake Plastics, Lenni, Pa.
  • This resin has a molecular weight of 5,000,000 g/mol and contains 500 ppm of calcium stearate.
  • the bar stock was obtained by the ram extrusion of the powder resin.
  • the bar stock was cut into “hockey puck” shaped cylinders (height 4 cm, diameter 8.5 cm).
  • the pucks were irradiated with an electron-beam incident to one of the circular bases of the pucks with a linear electron accelerator operated at 10 MeV and 1 kW (AECL, Manitoba Canada). Due to a cascade effect, electron beam irradiation results in a non-uniform absorbed dose profile.
  • Table 7. illustrates the calculated absorbed dose values at various depths in a specimen of polyethylene irradiated with 10 MeV electrons. The absorbed doses were the values measured at the top surface (surface of e-beam incidence).
  • This example illustrates a method of making UHMWPE that has a cross-linked structure and has substantially no detectable free radicals, by cold irradiating and then melting the UHMWPE.
  • the pucks described in Example 7 were irradiated at room temperature at a dose rate of 2.5 Mrad per pass to 2.5, 5, 7.5, 10, 12.5, 15, 17.5, 20, 30, and 50 Mrad total absorbed dose as measured on the top surface (e-beam incidence).
  • the pucks were not packaged and the irradiation was carried out in air.
  • the pucks were heated to 150° C. under vacuum for 2 hours so as to melt the polymer and thereby result in the recombination of free radicals leading to substantially no detectable residual free radicals.
  • the residual free radicals are measured by electron paramagnetic resonance as described in Jahan et al., J. Biomedical Materials Research 25:1005 (1991). The pucks were then cooled to room temperature at a rate of 5° C./min.
  • This example illustrates a method of making UHMWPE that has a cross-linked structure and has substantially no detectable free radicals, by irradiating UHMWPE that has been heated to below the melting point and then melting the UHMWPE.
  • the pucks described in Example 7 are heated to 100° C. in air in an oven.
  • the heated pucks are then irradiated with an electron beam to a total dose of 20 Mrad at a dose rate of 2.5 Mrad per pass.
  • the pucks are heated to 150° C. under vacuum for 2 hours, thereby allowing the free radicals to recombine leading to substantially no detectable residual free radicals.
  • the pucks are then cooled to room temperature at a rate of 5° C./min.
  • This example illustrates a method of making UHMWPE that has a cross-linked structure and has substantially no detectable free radicals, by irradiating UHMWPE that has been heated to below the melting point so as to generate adiabatic melting of the UHMWPE.
  • Example 7 Two pucks as described in Example 7 were packed in a fiberglass pouch (obtained from Fisher Scientific Co., Pittsburgh, Pa.) to minimize heat loss in subsequent processing steps.
  • the wrapped pucks were heated overnight in an air convection oven kept at 120° C.
  • the pucks were placed under an electron-beam as described in Example 7 and immediately irradiated to 21 and 22.5 Mrad, respectively.
  • the pucks were cooled to room temperature at a rate of 5° C./minute, at which point the fiberglass pouch was removed and the specimens analyzed.
  • This example illustrates various properties of the irradiated and unirradiated samples of UHMWPE bar stock GUR 415 obtained from Examples 8 and 10.
  • the tested samples were as follows: (i) test samples (pucks) from bar stock which was irradiated at room temperature, subsequently heated to about 150° C. for complete melting of polyethylene crystals, followed by cooling to room temperature (CIR-SM), (ii) test samples (pucks) from bar stock which was heated to 120° C. in a fiberglass pouch so as to minimize heat loss from the pucks, followed by immediate irradiation to generate adiabatic melting of the polyethylene crystals (WIR-AM), and (iii) control bar stock (no heating/melting, no irradiation).
  • Infra-red (IR) spectroscopy of the samples was performed using a BioRad UMA 500 infrared microscope on thin sections of the samples obtained from Examples 8 and 10.
  • the thin sections (50 ⁇ m) were prepared with a sledge microtome.
  • the IR spectra were collected at 20 ⁇ m, 100 ⁇ m, and 3 mm below the irradiated surface of the pucks with an aperture size of 10 ⁇ 50 ⁇ m 2 .
  • the peaks observed around 1740 to 1700 cm ⁇ 1 are associated with the oxygen containing groups.
  • a Perkin-Elmer DSC7 was used with an ice-water heat sink and a heating and cooling rate of 10 C./minute with a continuous nitrogen purge.
  • the crystallinity of the specimens obtained from Examples 8 and 10 was calculated from the weight of the sample and the heat of melting of polyethylene crystals measured during the first heating cycle.
  • E and w are the heat of melting (in Joules) and weight (in gram) of the specimen tested, respectively, and ⁇ H is the heat of melting of 100% crystalline polyethylene in Joules/gram (291 J/g).
  • the temperature corresponding to the peak of the endotherm was taken as the melting point. In some cases where there were multiple endotherm peaks, multiple melting points corresponding to these endotherm peaks have been reported.
  • the crystallinities and melting points for the specimens described in Examples 8 and 10 are reported in Tables 10 and 11.
  • the pin-on-disc (POD) experiments were carried out on a bi-axial pin-on-disc tester at a frequency of 2 Hz where polymeric pins were tested by a rubbing action of the pin against a highly polished Co—Cr disc.
  • the pins were then machined from the core of the pucks and tested on the POD such that the surface of e-beam incidence was facing the Co—Cr disc.
  • the wear tests were carried out to a total of 2,000,000 cycles in bovine serum.
  • the pins were weighed at every 500,000 cycle and the average values of weight loss (wear rate) are reported in Tables 12 and 13 for specimens obtained from Examples 8 and 10 respectively.
  • the samples were cut in cubes of size 2 ⁇ 2 ⁇ 2 mm 3 and kept submerged in xylene at 130° C. for a period of 24 hours.
  • An antioxidant 1% N-phenyl-2-naphthylamine
  • the swell ratio and gel content were calculated by measuring the weight of the sample before the experiment, after swelling for 24 hours and after vacuum drying the swollen sample. The results are shown in Tables 14 and 15 for the specimens obtained from the Examples 8 and 10.
  • This example illustrates the crystallinity and melting point at different depths of the cross-linked UHMWPE specimens obtained from Example 8 with 20 Mrad total radiation dose. Samples were taken at various depths from the cross-linked specimen. The crystallinity and the melting point were determined using a Perkin Elmer differential scanning calorimeter as described in Example 10(B). The results are shown in Table 16.
  • Example 7 Two pucks as described in Example 7 were irradiated at room temperature with a dose rate of 2.5 Mrad per pass to 17.5 Mrad total absorbed dose as measured on the top surface (e-beam incidence). The pucks were not packaged and the irradiation was carried out in air. Subsequent to irradiation, one puck was heated under vacuum to 150° C. for 2 hours, and the other puck was heated in air to 150° C. for 2 hours, so as to attain a state of no detectable residual crystalline content and no detectable residual free radicals. The pucks were then cooled to room temperature at a rate of 5° C./min. The pucks were then analyzed for the degree of oxidation as described in Example 10(A). Table 17 summarizes the results obtained for the degree of oxidation.
  • This example illustrates a method of making UHMWPE that has a cross-linked structure and has substantially no detectable free radicals, by cold irradiating with gamma-radiation and then melting the UHMWPE.
  • the pucks described in Example 7 were irradiated at room temperature at a dose rate of 0.05 Mrad/minute to 4 Mrad total absorbed dose as measured on the top surface (gamma ray incidence). The pucks were not packaged and irradiation was carried out in air. Subsequent to irradiation, the pucks were heated to 150° C. under vacuum for 2 hours so as to melt the polymer and thereby result in the recombination of free radicals leading to substantially no detectable residual free radicals.

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EP1202685A4 (fr) 2002-09-25
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ES2243980T3 (es) 2005-12-01
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CA2246342C (fr) 2008-04-22
PL328345A1 (en) 1999-01-18
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AU2050697A (en) 1997-09-02
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WO1997029793A1 (fr) 1997-08-21
EP0881919A1 (fr) 1998-12-09
CA2246342A1 (fr) 1997-08-21
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CN1211195A (zh) 1999-03-17
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EP1563857A3 (fr) 2008-06-04
ATE300964T1 (de) 2005-08-15
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CZ295935B6 (cs) 2005-12-14
DE69733879D1 (de) 2005-09-08

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